Electrosurgical systems and techniques for sealing tissue

ABSTRACT

An electrosurgical medical device and technique for creating thermal welds in the transected margin of engaged tissue. The working end of the invention carries a bi-polar electrode arrangement that provides a novel type of Rf current flow for tissue welding described as an subfascial-to-fascial (or medial-to-surface) bi-polar approach. The working end of the device carries an openable and closable jaw assembly with paired first and second jaws for engaging tissue. The paired jaws have an axial channel for receiving a sliding (blade) member for transecting the captured tissue. The paired jaws carry electrode surfaces having a common polarity so that Rf current will not flow directly between the jaws which engage the surface or fascial tissue layers. The transecting member, when fully extended after transecting the captured tissue, carries an elongate electrode of an opposing polarity that engages the medial or subfascial layers of the tissue. Thus, bi-polar current is directed to flow from the transecting member electrode that engages medial tissue layers to both jaws that engage opposing surface tissue layers to create effective current densities in the medial tissue layers, even when transecting thick tissue volumes or vessels with thick non-uniform fascial layers.

FIELD OF THE INVENTION

This invention relates to medical devices and techniques and more particularly relates to an electrosurgical device for thermally sealing or welding the margins of a transected tissue volume, as well as a novel jaw structure that allows substantially elongate jaws to provide high compressive forces the captured tissue volume.

BACKGROUND OF THE INVENTION

In various open and laparoscopic surgeries, it is necessary to seal or weld the margins of transected tissue volumes, for example, a transected blood vessel or a tissue volume containing blood vessels. In a typical procedure, a deformable metal clip may be used seal a blood vessel, or a stapling instrument may be used to apply a series of mechanically deformable staples to seal the transected edge a larger tissue volume. Such mechanical devices may create a seal that leaks which can result in later complications.

Various radiofrequency (Rf) surgical instruments for sealing transected structures have been developed. For example, FIG. 1A shows a sectional view of paired electrode-jaws 2 a and 2 b of a typical prior art bi-polar Rf grasper grasping a blood vessel. In a typical bi-polar jaw arrangement, each jaw face comprises an electrode and Rf current flows across the tissue between the first and second polarities in the opposing jaws that engage opposing exterior surfaces of the tissue. FIG. 1A shows typical lines of bi-polar current flow between the jaws. Each jaw in FIG. 1A has a central slot adapted to receive a reciprocating blade member as is known in the art for transecting the captured vessel after it is sealed.

While bi-polar gapers as in FIG. 1A can adequately seal or weld tissue volumes that have a small cross-section, such bi-polar instruments are often ineffective in sealing or welding many types of anatomic structures, e.g., (i) substantially thick structures, (ii) large diameter blood vessels having walls with thick fascia layers f (see FIG. 1A), (iii) bundles of disparate anatomic structures, (iv) structures having walls with irregular fibrous content.

As depicted in FIG. 1A, a relatively large diameter blood vessel falls into a category that is difficult to effectively weld utilizing prior art instruments. A large blood vessel wall has substantially thick, dense and non-uniform fascia layers underlying its exterior surface. As depicted in FIG. 1A, the fascia layers f prevent a uniform flow of current from the first exterior surface S to the second exterior surface 9 of the vessel that are in contact with electrodes 2 a and 2 b. The lack of uniform bi-polar current across the fascia layers f causes non-uniform thermal effects that typically result in localized tissue desiccation and charring indicated at c. Such tissue charring can elevate impedance levels in the captured tissue so that current flow across the tissue is terminated altogether. FIG. 1B depicts an exemplary result of attempting to weld across a vessel with thick fascia layers f with a prior art bi-polar instrument. FIGS. 1A-1B show localized surface charring c and non-uniform weld regions w in the medial layers m of vessel. Further, FIG. 1B depicts a common undesirable characteristic of prior art welding wherein thermal effects propagate laterally from the targeted tissue causing unwanted collateral (thermal) damage indicated at d.

A number of bi-polar jawed instruments adapted for welding and transecting substantially small structures have been disclosed, for example: U.S. Pat. No. 5,735,848 to Yates et al.; U.S. Pat. No. 5,876,410 to Schulze et al.; and U.S. Pat. No. 5,833,690 to Yates et al. One other similar bi-polar instrument was disclosed by Yates et al. in U.S. Pat. No. 5,403,312. In that patent, paired bi-polar electrodes are provided in left and right portions of a jaw member to induce current flow therebetween. It is not known whether a jaw having the left-to-right or side-to-side bi-polar current flow of U.S. Pat. No. 5,403,312 was ever tested, but it seems likely that such an instrument would confine current flow to the tissue's exterior surface and facial layers f (see FIG. 1B), thus aggravating the desiccation and charring of such surface layers.

What is needed is an instrument working end that can utilize Rf energy in new delivery modalities: (i) to weld a transected margin of a substantially thick anatomic structure; (ii) to weld or seal a margin of a blood vessel having thick or non-uniform fascia layers; (iii) to weld or seal tissue volumes that are not uniform in hydration, density and collagenous content; (iv) to weld a transected margin of a bundle of disparate anatomic structures; and (v) to weld a targeted tissue region while substantially preventing collateral thermal damage in regions lateral to the targeted tissue.

SUMMARY OF THE INVENTION

The object of the present invention is to provide a novel technique—and an instrument working end capable of practicing the technique—for causing controlled Rf energy delivery and controlled thermal effects in a transected margin of tissues with thick facial layers, or other tissue with non-uniform fibrous content. For example, larger diameter blood vessels are a targeted application since such vessels have thick facials layers that can prevent uniform current flow and uniform resistive heating of the tissue.

As background, the biological mechanisms underlying tissue fusion by means of thermal effects are not folly understood. In general, the delivery of Rf energy to a captured tissue volume elevates the tissue temperature and thereby at least partly denatures proteins in the tissue. The objective is to denature such proteins, including collagen, into a proteinaceous amalgam that intermixes and fuses together as the proteins renature. As the treated region heals over time, the so-called weld is reabsorbed by the body's wound healing process.

In order to create an effective weld in a tissue volume with substantial fascial layers, it has been found that several factors are critical. The objective is to create a substantially even temperature distribution across the targeted tissue volume to thereby create a uniform weld or seal. Fibrous tissue layers (i.e., fascia) conduct Rf current differently than adjacent less-fibrous layers, and it is believed that differences in extra cellular fluid contents in such adjacent tissues contribute greatly to the differences in electrical resistance. It has been found that by applying very high compressive forces to a tissue volume comprising fascia layers and adjacent non-fibrous layers, the extracellular fluids either migrate from the non-fascial layers to the fascial layers or migrate from the captured tissue to collateral regions. In either event, high compressive forces tend to make the resistance more uniform regionally within the captured tissue volume. Further, it is believed that high compressive forces (i) cause protein denaturation at a lower temperature which is desirable, and (ii) cause enhanced intermixing of denatured proteins thereby creating a more effective weld upon tissue protein renaturation.

Of equal importance, it has been found that that a critical factor in creating an effective weld across adjacent fibrous (fascia) layers and non-fibrous (medial) layers is the deliver of bi-polar Rf energy from electrode surfaces engaging the medial layers and the surface or fascia layers. In other words, effective current flow through the fascia layers is best accomplished by engaging electrodes on opposing sides of the fascial layers. Prior art jaw structures that only deliver bi-polar Rf energy from outside the surface or fascial layers cannot cause effective regional heating inward of such fascial layers. For this reason, the novel technique causes Rf current flow to-and-from the medial (or just-transected) non-fascia layers of tissue at the interior of the structure, rather than to-and-from exterior surfaces only as in the prior art. This method is termed herein a medial-to-surface bi-polar delivery approach or a subfascia-to-fascia bi-polar approach.

Another aspect of the invention provides means for increasing the area of the engagement interface between an electrode and the just-exposed medial tissue layers. This is accomplished by providing a wedge-like slidable member having a electrode surface for compressing the just-transected tissue volume against inner faces of the paired jaw members.

More in particular, the working end of the instrument carries a jaw assembly with paired first and second jaws for engaging and compressing tissue along a line targeted for transection. The transected tissue margins thereby expose medial tissue layers m that can be engaged by an electrode. The jaw structure is moveable between a first (open) position and a second (closed) position by a slidable blade member that serves two functions: (i) to transect the captured tissue, and (ii) to contemporaneously lock together the elongate jaws by means of “I ” -beam flanges that span both sides of the paired jaws.

The combination of the first and second jaws together with a cooperating slidable transecting (or blade) member further provides a novel electrode arrangement that can accomplish the electrosurgical welding technique of the invention. The opposing jaws carry electrodes surfaces coupled to an Rf generator that have a common polarity. In other words, Rf current does not flow directly from the first jaw to the second jaw (in contrast to prior art, see FIG. 1A). Rather, the extension portion of the slidable transecting member carries, or comprises, an electrode of an opposing polarity. Thus, when the transecting member is moved to the extended position after transecting the engaged tissue volume, the elongate electrode carried by the transecting member will thus engage the medial or interior layers of the transected margin. By this means, for the first time, bi-polar current flows can be directed from the transecting member that engages medal or sub-fascial tissue layers to both jaw faces that engage opposing surface or fascial tissue layers of the targeted tissue volume. It has been found that by engaging the medial portion of a just-transected structure with a first bi-polar electrode, and an exterior of the structure engaged with a second cooperating electrode, substantially uniform current flow through thick or non-uniform fascia layers can be accomplished. This novel medial-to-surface bi-polar approach of the invention also seems to greatly reduce tissue charring, and substantially prevents collateral thermal damage in the tissue by reducing stray Rf current flow through tissue lateral to the engaged tissue.

Of particular interest, the invention provides other (optional) features that enhance the effectiveness of an medial-to-surface bi-polar approach. More in particular, it has been found that increasing the electrode engagement area with the medial tissue layers can enhance thermal effects for tissue welding, For this reason, the elongate transecting member electrode may be configured as a wedge-type with an increasing cross-section that is adapted to plow into the medial tissue layers thereby increasing the electrode-tissue engagement area.

Also of particular interest, the invention provides means for compressing the engaged tissue between the electrode surface engagements, which has been found to assist in creating an effective weld. Such tissue compression again can be accomplished by using the increasing cross-section of the slidable transecting member to progressively press the tissue margins against a cooperating shape formed into the jaws.

In another embodiment of the invention, the jaw assembly further includes components of a sensor system which together with a power controller can control Rf energy delivery during a tissue welding procedure. For example, feedback circuitry for measuring temperatures at one or more temperature sensors in the jaws may be provided. Another type of feedback circuitry may be provided for measuring the impedance of tissue engaged between the transecting member and a jaw. The power controller may continuously modulate and control Rf delivery in order to achieve (or maintain) a particular parameter such as a particular temperature in tissue, an average of temperatures measured among multiple sensors, a temperature profile (change in energy delivery over time), or a particular impedance level or range.

Additional objects and advantages of the invention will be apparent from the following description, the accompanying drawings and the appended claims.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is an illustration of current flow between the paired jaws of a prior art bi-polar radiofrequency device in a method of sealing a large blood vessel having substantially thick fascia layers.

FIG. 1B illustrates representative weld effects of the bi-polar current flow of FIG. 1A

FIG. 2 is a perspective cut-away view of the Rf working end of the present invention with the cooperating jaw members in a first (open) position and a sliding transecting or blade member in a first (retracted) position.

FIG. 3 is a different perspective cut-away view of the working end of FIG. 2 with the cooperating jaw members in a second (closed) position and the sliding transecting member in second (extended) position.

FIG. 4 is a perspective view of the slidable blade member of the working end of FIGS. 2-3 in first and second positions with the jaw members not shown.

FIG. 5A is an enlarged cross-sectional view showing an exemplary shape of the jaw faces of FIG. 2 taken along line 5A—5A and depicting a tissue engagement plane.

FIG. 5B is an alternative cross-sectional shape (similar to FIG. 5A) of jaw faces defining an alternative engagement plane.

FIG. 6 is a view of the shape of the engagement plane of a prior art electrosurgical jaw wherein the jaw faces extend generally as a radial of the central axis.

FIGS. 7A-7B are sectional illustrations of steps of practicing the method of the invention in moving a jaw assembly to a closed position to provide high compressive forces in providing substantial electrode contact with surface layers and medial layers of the engaged tissue:

FIG. 7A being a sectional view of a large blood vessel with thick fascia layers being (i) captured and compressed by the jaw structure, and (ii) being transected by the leading edge of the blade member;

FIG. 7B being a sectional view of the increased diameter of an extension member electrode engaging a broad surface of the medial tissue layers as such layers are compressed outwardly against the cooperating jaw faces.

FIGS. 8A-8B are sectional illustrations of steps of practicing the method of delivering bi-polar Rf current flow to seal or weld the transected margins the engaged blood vessel of FIGS. 7A-7B;

FIG. 8A being an illustration of Rf current flow from electrodes in contact with medial tissue layers to electrodes in contract with surface tissue layers; and

FIG. 8B being an illustration of the thermal weld effects caused of the novel form of bi-polar current flow of FIG. 8A.

FIG. 9A is a perspective view of a Type “B” embodiment of electrosurgical working end (similar to FIG. 4) that provides a secondarily actuated slidable electrode member for compressing tissue laterally outward while providing increased electrode engagement area with medial tissue layers.

FIG. 9B is an enlarged sectional view of the Type “B” device of FIG. 9A taken along line 9B—9B of FIG. 9A (showing one side of the jaw members in plain view) illustrating an increased area for electrode engagement with medial tissue layers.

FIG. 10 is a sectional view Type “C” working end of the present invention similar to the working end of FIG. 9A with thermoelectric cooling elements for preventing collateral thermal damage to tissue during the tissue-welding process.

DETAILED DESCRIPTION OF THE INVENTION

Type “A” Electrosurgical Working End for Sealing or Welding Tissue. Referring to FIG. 2, the working end 5 of an exemplary Type “A” embodiment is shown that is adapted for sealing or welding a tissue volume, such as a blood vessel, in an open or endoscopic procedure. The working end 5 has paired jaw portions 8A and 8B that are carried at the distal end of elongate introducer portion 10 (with handle not shown) extending along central longitudinal axis 15. In this exemplary embodiment, the structural component of introducer portion 10 has a cylindrical cross-section and comprises a thin-wall tubular sleeve 16 that extends from a proximate handle (not shown). The diameter of sleeve 16 may range from about 3 mm. to 10 mm., e.g., to cooperate with a standard endoscopic Tracy sleeve. The handle may be any type of pistol-grip or other type of handle known in the art that carries actuator levers or slides as described below.

The first jaw member 8A is actuated from the first open position of FIG. 2 to the second closed position of FIG. 3 by a novel jaw-closing system that applies very high compressive forces to captured tissue volumes over the length of substantially elongate jaws. Referring to FIG. 2, it can be seen that the upper (first) jaw member 8A is actuatable about pivot pins 17 a and 17 b to open and close relative to the lower (second) jaw member 8B that in this exemplary embodiment is configured as a fixed (non-actuatable) jaw. The pivot pins 17 a and 17 b are fit into a proximal portion 19 of lower jaw body member 20 that is fixedly coupled to the distal end of thin-wall sleeve 16.

In this embodiment, the jaw structure is moved from the first open position (FIG. 2) to the second closed position (FIG. 3) by a dual-action jaw-closing system. In FIG. 2, it can be seen that upper jaw member 8A has arcuate slots 22 a and 22 b in arm portions 23 a and 23 b. Reciprocatable actuator rods 24 a and 24 b carry pins 26 a and 26 b in their distal ends that slide in arcuate slots 22 a and 22 b of the jaw arms to initially actuate upper jaw 8A toward a closed position (FIG. 3) from the open position of FIG. 2. It can be seen that the slidable actuator rods 24 a and 24 b comprise a first component of the jaw-closing system. The proximal ends of actuator rods 24 a and 24 b are coupled to a first actuator known in the art and carried in the handle portion (e.g., a lever arm or squeeze grip) that translates the rods to and fro. These rods 24 a and 24 b slide through parallel aligned bores 27 a and 27 b in body member 20. This first mechanism for actuating upper jaw 8A is adapted to cause an initial movement of the jaw toward the second closed position (see FIG. 3). A second actuator mechanism, described below, is provided for locking the paired elongate jaws in the second closed position (FIG. 3) to provide high tissue-compressing forces over the entire length of the elongate jaws, and to open the jaws. The axial length of jaws 8A and 8B indicated at a may be any suitable length depending on the anatomic structure targeted for transection and sealing and may range from about 100 mm. or more, for example for resecting and sealing lung, to as little as 5.0 mm. for a micro-surgery.

As can be seen best in FIG. 2, the upper and lower jaws 8A and 8B have axial slots therein indicated at 28 a and 28 b that cooperate to receive a thin translatable blade member 30 with sharp edge 31 for transecting tissue captured in the jaw assembly. To better explain the second mechanism for closing the jaws, FIG. 4 shows introducer sleeve 16 with blade member 30 (without showing jaws) in its first retracted position and its second extended position. The proximal end of extension member 32 (not shown) is coupled to a second actuation means known in the art and carried in the handle portion (not shown) of the device to translate blade member 30 distally and proximally. The actuator may be any type of lever arm or slider adapted to translate the blade member. The distal end 33 of extension member 32 is connected to the blade member. The blade portion of the assembly of FIG. 4 has an “I”-beam type cross-section 37 with upper flange member 35 a and lower flange member 35 b. Of particular interest, as will described below, the upper and lower flanges 35 a and 35 b serve as functional components of the dual-action jaw-closing mechanism. The upper and lower flanges 35 a and 35 b are fixed to blade member 30 by any suitable means such as fittings with pins, adhesives or the like. Further, as can be seen in FIGS. 2 and 4, the rounded leading edge 36 a of upper flange portion 35 a is adapted to push against flat surface 38 a of upper jaw 8A as a cam to thus push the jaw toward the closed position of FIG. 3. Besides being adapted to push moveable jaw 8A toward the closed position, it can be understood that the paired upper and lower flanges 35 a and 35 b are adapted to lock the distal portions 40 of the jaws in the second closed position. As can be seen in FIG. 4 and FIG. 5A, the inner flees 42 a and 42 b of flanges 35 a and 35 b of the “I”-beam form 37 are spaced apart a fixed dimension and are thus adapted to engage against outer surfaces 35 a and 38 b of the jaws to thereby lock the distal jaw portions 40 together. The dimension (indicated at b in FIG. 4) between flange inner faces 42 a and 42 b determines and controls the thickness of the tissue that is compressed between the jaw faces. In sum, the proximal jaw portions 44 (FIG. 3) are maintained together by the pivot pins 17 a and 17 b to define a predetermined gap dimension g between jaw face portions 46 a and 46 b in the closed position, while the distal jaw portions 40 are locked together by the flanges of the blade member. The combination blade and jaw-locking mechanism built into the blade member 30 (see FIG. 4) allows very elongate jaws to be locked together at distal ends thereof to thereby apply high compressive forces to captured tissue—which forces could not be achieved with a conventional jaw-closing mechanism as used is prior art graspers. This first and second jaw-closing mechanisms are preferably actuated from a single suitable actuator (e g., a lever arm or squeeze grip) that (i) can move actuator rods 24 a and 24 b proximally to initiate the jaw closing process, and (ii) move the extension member 32 coupled to blade member 30 distally to close and lock the jaws in the second closed position (see FIG. 3). Such dual-actuation mechanical systems are known in the art and need not be described in detail herein.

Referring to FIG. 4, other novel features and functions of the blade member or assembly can now be described In this preferred embodiment, the extension member 32 of the blade assembly has a surface comprising an electrode 50 that is of any suitable conductive material. As will be described below, this core electrode or central electrode 50 is adapted to cooperate with electrodes 55A and 55B in the upper and lower jaws, respectively. The core electrode 50 is coupled to electrical source 60 by a lead wire indicated at 62 in FIGS. 2-3. As can be seen best in FIG. 4, the extension member 32 has a distal tapered portion 63 that is fixedly coupled to blade member 30. The tapered portion 63 rapidly transitions to a greater cross-sectional medial portion 64 of extension member 32 that serves a compression member to press transected tissue outwardly against cooperating faces 66 a and 66 b of the jaws. In this embodiment, the cross-section of extension member 32 and electrode 50 is round, but it should be appreciated that any shape is possible that is designed to cooperate with the shape of cooperating jaws faces to compress tissue in the method of the invention described below. This core electrode 50 is adapted to contact and engage the inner or medial layers m of just-transected tissue, as well as to laterally compress the just-transected tissue against jaw faces 66 a and 66 b, as will be described the practice of the method of the invention.

Now turning to FIG. 5A, the novel shapes and surfaces of electrodes faces 55A and 55B in engaging faces 46 a and 46 b of jaws 8A and 8B can be described FIG. 5A shows that the paired jaws in the second closed position generally define an open central channel portion indicated at 65 that has a cross-sectional shape that cooperates with the cross-sectional shape of core electrode 50 (phantom view), in this case having a round cross-section. The distal ends 67 a and 67 b of jaws 8A and 8B extend around, and define, the distal end open channel 65 within the closed jaws as can be seen in FIG. 3.

FIG 5A further shows that engaging faces 46 a and 46 b of jaws 8A and 8B define an engagement plane P (dashed line) that represents the plane in which targeted tissue is captured or engaged between the jaws before being transected by blade 30, as well as during Rf energy delivery. Of particular interest, the engagement plane P: (i) has a non-linear form or non-planar from transverse to central axis 15 of the jaw structure, and/or (ii) has no portions that comprise a radial r of the axis 15 of the jaws (see FIG. 5A). In prior art jaws, such an engagement plane P of the jaws typically is linear and also comprises a radial of a central axis of the jaws as shown in FIG. 6. By the term radial, it is meant that a radial line or plane is orthogonal to the central axis of the jaws and also be termed a radius (see FIG. 6). As can be seen in FIG. 6, such a radial r thus defines the shortest possible distance from central axis 15 to an exterior surface or edge of the jaw structure. In the present invention, it has been found that thermal welds are enhanced in medial-to-surface Rf current flows when increased electrode surface areas are provided for engaging tissue between the upper and lower jaws. The novel manner of providing such increased electrode engagement area, within a small diameter jaw form, is to not provide an engagement plane P that is a simple radial r of central jaw axis. Rather, the preferred embodiment of the invention provides non-radial forms for such an engagement plane P. As can be seen in FIG. 5A, a preferred engagement plane P is provided that extends at angles to a radial r thereby providing an increased dimension across the jaw faces 46 a and 46 b that carry the surfaces of electrodes 55A and 55B. While FIG. 5A depicts an engagement plane P that is suitable for accomplishing the method of the invention, FIG. 5B depicts another engagement plane P that has jaw faces 46 a and 46 b that define an undulating form and thus is somewhat further removed from a radial form.

The sharp leading edge 31 of blade 30 shown in FIG. 4 is preferred for cutting tissue. Alternatively, the leading edge of blade member 30 may be an electrode element that operates at high Rf intensities suitable for cutting tissue as is known in the art. For example, for tissue cutting purposes, Rf frequencies may range from 500 kHz to 2.5 MHz, with power levels ranging from about 50 W. to 750 W., and open circuit voltages ranging as high as 9 Kv. In this alternative configuration, such an electrode cutting element preferably is insulated from core electrode 50 that cooperates with paired electrodes 55A and 55B. Alternatively, the working end may have a singular electrode that is adapted to both transect the captured tissue and thereafter cooperate with electrodes 55A and 55B to seal the tissue as will be described below.

Of particular interest, it can now be seen the translation of medial portion 64 of the extension member 32 provides issue-compressing means for compressing a medial portion m of the transected and exposed margin of the anatomic structure between cooperating surfaces. More in particular, FIGS. 7A-7B illustrate sectional views of the exemplary cross-sectional shape formed into engaging surfaces 66 a and 66 b of central channel 65 of the jaws and central electrode 50. Referring back to FIG. 4, it can be seen that extension member 32 and the surface of electrode 50 increase in cross-sectional dimension from distal taper portion 63. Thus, the extension member 32, besides functioning to compress the medial tissue m of the vessel walls outwardly against the inwardly-facing jaw faces 66 a and 66 b, also functions to increase the surface area of electrode 50 in contact with medial tissue layers m of the transected structure. As shown schematically in FIGS. 7A-7B, electrodes 55A and 55B in the paired jaws have a common (first) polarity and are coupled to electrical generator 60 and controller 70. The cooperating central electrode 50 carried by extension member 32 has an opposing (second) polarity, and again is coupled to generator 60 and controller 70. FIG. 7B thus indicates that bi-polar Rf current will flow between the central extension member electrode 50 and either jaw face 46 a and 46 b (i.e., electrodes 55A and 55B carried therein). The views of FIGS. 2 and 3 indicate that a current carrying wire lead 62 extends from electrical source 60 to extension member electrode 50. Leads 74 a and 74 b extend from Rf source 60 to each of electrode elements 55A and 55B carried within the jaws. The electrodes are of any suitable material such as aluminum, stainless steel, nickel titanium, platinum, gold, or copper. Each electrode surface preferably has a micro-texture (e.g., tiny serrations or surface asperities, etc.) for better engaging tissue and for delivering high Rf energy densities in engaged tissues as is known in the art. The bi-polar Rf current may be switched on and off by a foot pedal or any other suitable means such as a switch in handle (not shown).

Another embodiment of the invention (not shown) includes a sensor array of individual sensors (or a single sensor) carried in any part of the jaw assembly that is in contact with the tissue targeted for welding. Such sensors preferably are located slightly spaced apart from electrodes 55A-55B for the purpose of measuring temperatures of tissue adjacent to the electrodes during a welding procedure. It should be appreciated however that the sensors also may measure temperature at the electrodes. The sensor array typically will consist of thermocouples or thermistors (temperature sensors that have resistances that vary with the temperature level). Thermocouples typically consist of paired dissimilar metals such as copper and constantan which form a T-type thermocouple as is known in the art Such a sensor system can be linked to feedback circuitry that together with a power controller can control Rf energy delivery during a tissue welding procure. The feedback circuitry can measure temperatures at one or more sensor locations, or sensors can measure the impedance of tissue, or voltage across the tissue, that is engaged between the transecting member and a jaw. The power controller then can modulate Rf delivery in order to achieve (or maintain) a particular parameter such as a particular temperature in tissue, an average of temperatures measured among multiple sensors, a temperature profile (change in energy delivery over time), a particular impedance level or range, or a voltage level as is known in the art.

Operation and use of the working end 5 of FIGS. 2-3 in performing a method of the invention can be briefly described as follows. FIG. 7A shows a targeted tissue volume t that is captured between first and second jaws 8A and 8B The targeted tissue t may be any soft tissue or anatomic structure of a patient's body and FIGS. 7A-7B depict a large diameter blood vessel 80 with vessel walls 82 having thick fascia layers indicated at f underlying exterior surfaces s, medial tissue layers m and endothelial layers en. FIG. 7A depicts the blood vessel as it is transected by blade member 30. FIG. 7A further shows the paired electrodes 55A and 55B of first and second jaw faces 46 a and 46 b engaging exterior surfaces s of the targeted tissue t thereby defining electrode engagement areas indicated at e₁ (collectively) between the first polarity electrodes 55A-55B and the exterior surfaces s of the vessel.

Referring to FIG. 7B, it can be easily understood that progressive slidable movement of blade 30 causes the increased cross-section of core electrode 50 to plow into walls 82 of the vessel to press the medial tissue m between the extension member 32 and the cooperating sides 66 a and 66 b of axial channel 65 in the opposing jaw members. At the same time, the slidable extension member 32 carries electrode surface 50 that is pressed into contact with the endothelium en and medial tissue volumes m to thereby provide a broad engagement surface indicated at e₂ between the second polarity core electrode 50 and such medial tissue m (defined as including endothelium en). In FIG. 7A, the electrodes 55A and 55B are shown as being insulated from the structural component of jaws, but it should be appreciated that these electrodes 55A and 55B may comprise the structural component of the jaws, for example in very small instruments. Thus, in such an embodiment, the electrode engagement surface area e₁ of electrodes 55A and 55B can comprise substantially the entire jaw face that contacts the targeted tissue.

Now tuning to FIG. 8A, an illustration is provided that indicates the sealing or welding effect that is achievable by the medial-to-surface bi-polar current flow (or vice versa) indicated by arrows A. It has been found that a substantially uniform weld w can be created across the entire tissue volume captured between the engagement surfaces e₁ and e₂ of the jaw electrodes 55A-55B and central electrode 50, respectively. In other words, the sectional illustration of FIG. 8B shows that a weld w can be created where the proteins (including collagen) are denature intermixed under high compressive forces, and then permanently fused upon cooling to seal or weld the margin of the transected vessel. Further, it is believed that the desired weld effects can be accomplished substantially without collateral thermal damage to adjacent tissues indicates at 92 in FIG. 8B.

2. Type “B” Working End for Scaling or Welding Tissue. A Type “B” working end 105 is substantially the same as shown in FIGS. 2-3 with the addition of an independently actuatable extension sleeve member 122 that carries core electrode 50 as shown in FIGS. 9A-9B. In the Type “B” system of FIG. 9A, all component parts that are identical to those of the Type “A” embodiment have the same reference numeral. FIG. 9A shows the blade member 30 is coupled to an inner extension member 132 that can be translated from a retraced position to an extended position (see FIG. 9A) to transect captured tissue as described previously. FIG. 9A shows the blade assembly without the jaw structure to illustrate that extension sleeve member 122 is adapted to independently slide over inner extension member 132. By separating the components of the invention that actuate the blade member 30 and the extension sleeve 122 that carries the core electrode 50 as well as tissue-compression mean, the level of tissue compression can be better controlled. The extension sleeve 122 has a distal taper indicated at 134 with core electrode 50 covering the surface extension sleeve 122. The extension sleeve 122 is actuatable from a first retraced position to an extended position (see FIG. 9A) by an independent lever or slider mechanism in the handle (not shown) of the instrument. It can be easily understood that the independently actuated extension sleeve 122 is adapted to plow into and compress the transected margin of the engaged tissue outwardly against the cooperating jaw surfaces. Referring to FIG. 9B, an enlarged sectional view of one side of the jaw structure is shown that provides increased electrode engagement surfaces e₁ and e₂. In this embodiment, the electrode engagement area e₁ at the exterior surface s of the vessel is enhanced by cooperating undulations 77 in jaws faces 146 a and 146 b. Further, the exemplary embodiment of FIG. 9B shows that electrode engagement area e₂ is enhanced by providing an oval shape to the core electrode 50 that cooperates with jaw faces 166 a and 166 b. The embodiment of FIG. 9B also shows that the entire jaw members may comprise electrodes 55A and 55B, which may particularly suitable for very small diameter instruments.

3. Type “C” Working End for Sealing Tissue. FIG. 10 shows an alternative embodiment of a working end 205 and jaw structure that performs the previously-described tissue welding methods of the invention. The transecting blade member 30 cooperates with paired jaw members 208A and 208B similar to the previous embodiments. FIG. 10 shows that a novel feature of this embodiment comprises active tissue-cooling means carried within at least one lateral portion 211 of the lower jaw 208B for cooling tissue volumes collateral to the transected margin that is targeted for welding. The tissue-cooling means comprises thermoelectric cooling elements (or Peltier elements) 210 comprising at least one layer of semiconductor blocks (e.g., bismuth telluride) within inner and outer heat conduction layers 216 a and 216 b of a plastic or other material that in not electrically conductive. The use of such semiconductor cooling of tissue engaged by jaw members of a working end (together with thermal energy delivery means) for tissue welding was first disclosed by an author in co-pending U.S. patent application Ser. No. 09/110,065 filed Jul. 3, 1998, which is incorporated herein by this reference. Such semi-conductor cooling elements are coupled to leads and a direct current electrical source (not shown) as is known in the art for drawing heat from the engaged tissue and radiating the heat into the environment from the outer surfaces 216 a and 216 b. The desired parameters for such semi-conductor cooling elements can be derived from engineering manuals known in the art (see, e.g., Thermoelectric Product Catalog and Technical Reference Manual published by Ferrotec America Corp., 1050 Perimeter Rd., Manchester, N.H. 03103). FIG. 10 further shows that the jaws of the invention optionally may be asymmetric. That is, the jaws may be designed to seal only one margin of the transected tissue, as would be useful in a lung resection or any other procedure in which it is not necessary to seal the margin of tissue that is transected and removed

Another embodiment of the invention (not shown) may combine linear stapling means with the welding techniques of the invention. In other words, rows of staples together with staple-driving means can be carried in elongate jaws lateral to the electrodes 55A-55B (see FIG. 7A) carried in the jaws. Such stapling means are known in the art (see, e.g., U.S. Pat. No. 5,403,312 to Yates et al).

Although particular embodiments of the present invention have been described above in detail, it will be understood that this description is merely for purposes of illustration. Specific features of the invention are shown in some drawings and not in others, and this is for convenience only and any feature may be combined with another in accordance with the invention. Further variations will be apparent to one skilled in the art in light of this disclosure and are intended to fall within the scope of the appended claims. 

What is claimed is:
 1. A jaw assembly of a surgical instrument, comprising: an instrument working end carrying first and second jaws actuatable between a first open position and a second closed position, the jaws in the closed position defining a longitudinal axis and wherein the jaws further define exterior faces and interior jaw faces; an axially-extending member that is actuatable from a first retracted position to a second extended position in an axial channel defined by said first and second jaws; and said axially-extending member defining paired flange portions with first and second inner faces that engage said exterior faces of said jaws; wherein actuation of said axially-extending member toward the second extended position from the first retracted position thereby actuates the jaws toward the second closed position from the first open position.
 2. The jaw assembly of claim 1 wherein the distal portion of the axially-extending member carries a blade member for transecting tissue.
 3. The jaw assembly of claim 1 wherein the distal portion of the axially-extending member carries a cutting electrode for transecting tissue.
 4. The jaw assembly of claim 1 wherein said cooperating interior jaw faces carry electrodes of a common polarity and the axially-extending member carries an electrode of an opposing polarity.
 5. The jaw assembly of claim 1 wherein either of said jaws or said axially-extending member carries a temperature sensor.
 6. An electrosurgical instrument, comprising: an introducer body having a distal working end; first and second jaws actuatable between a first open position and a second closed position that defines an axis, each jaw defining a jaw engagement surface that carries an electrode for engaging an exterior surface of tissue captured therebetween; a first axially-extending member carrying tissue-transecting means that is actuatable within an axial channel in said first and second jaws, a second axially-extending member carrying an electrode that is actuatable within an axial channel in said first and second jaws, the electrode for engaging an interior surface of tissue that is transected by said first axially-extending member; and wherein the electrodes in jaw engagement surfaces have a common polarity and the electrode carried in the second axially-extending member has an opposing polarity.
 7. An electrosurgical instrument, comprising: an introducer body having a distal working end; first and second jaws actuatable between a first open position and a second closed position that defines an axis, each jaw defining a jaw engagement surface that carries an electrode for engaging an exterior surface of tissue captured therebetween; a first axially-extending member carrying tissue-transecting means that is actuatable within an axial channel in said first and second jaws, a second axially-extending member carrying an electrode that is actuatable within an axial channel in said first and second jaws, the electrode for engaging an interior surface of tissue that is transected by said first axially-extending member; and wherein a distal portion of the second axially-extending member increases in cross-section in the proximal direction. 